Differential pressure type pulmonary function instrument flow calculation method and device and storage medium

Abstract

The invention discloses a differential pressure type pulmonary function instrument flow calculation method and device and a storage medium. The method comprises the following steps: acquiring pressure differences corresponding to different flows measured in real time by a pressure tapping device of a differential pressure type pulmonary function instrument in a calibration stage, and respectively storing pressure difference data and flow data which are measured in real time into a pressure difference array and a flow array to form a reference table; acquiring actually-measured pressure difference data of a pressure tapping device of the pressure difference type pulmonary function instrument in the use stage, and judging where the actually-measured pressure difference data falls into the pressure difference array of the reference table; and calculating the flow corresponding to the actually measured pressure difference data by using an interpolation method based on the reference table. The method has the remarkable advantages in the aspects of calculation accuracy, calculation efficiency, system real-time performance, system stability, cost applicability and the like, and is particularly suitable for the differential pressure type pulmonary function instrument with the nonlinear screen pressure tapping air channel.

Description

Technical Field

[0001] The present invention relates to the technical field of pulmonary function meters, and in particular, to a flow calculation method, device and computer-readable storage medium for a differential pressure type pulmonary function meter. Background Art

[0002] Currently, the mainstream pulmonary function meters on the market are mainly based on the principle of differential pressure flow meters. The flow rate is measured by using the corresponding relationship between the pressure drop of the air flow and the flow velocity in a flow pipe with a certain shape. The differential pressure flow meter includes two parts: a pressure-taking device and a differential pressure sensor. According to different measurement principles, the pressure-taking device can be divided into various different forms such as throttling type, orifice plate type, pitot tube type and venturi tube. For example, Chinese patents CN201710391273.7, CN202111041601.3 and CN201910929756.7 respectively record pulmonary function meters with differential pressure sensors.

[0003] The pressure-taking device of the above-mentioned pulmonary function meter adopts the principle of converting differential pressure to flow rate, and usually uses fluid mechanics formulas for conversion. For example, in patent CN207837551U, it is proposed that the flow rate and the differential pressure before and after the throttling device satisfy a power function relationship, but the throttling device is difficult to detect low flow rates, so a screen pressure-taking airway appears. For example, the airway in the large lung detection of the Jaeger pulmonary function meter, the differential pressure at both ends of the screen and the flow rate maintain a linear relationship, but the manufacturing process of this airway is relatively complex and the cost is very high. Patent CN218484563U also uses a screen pressure-taking airway, but it only maintains linearity within 0 - 1500 ml / s.

[0004] For a screen pressure-taking airway where the differential pressure at both ends and the flow rate are non-linear, only by measuring the actual data and then fitting a curve can a conversion formula be obtained. In order to improve the accuracy, the formula fitting is relatively complex, and some even require segmented processing. The MCU software needs to calculate the flow rate corresponding to the differential pressure while collecting the data of the differential pressure sensor. Such calculations usually bring a large computational pressure to the embedded processor MCU with relatively small computing power, consume system time, and affect the real-time performance of the calculation results.

[0005] Therefore, especially for a differential pressure type pulmonary function meter with a non-linear screen pressure-taking airway, how to accurately calculate the flow rate while reducing the computational complexity is a difficult problem that those skilled in the art are committed to solving. Summary of the Invention

[0006] The technical problem to be solved by the embodiments of the present application is: how to accurately calculate the flow rate of a differential pressure type pulmonary function meter while reducing the computational complexity.

[0007] To solve the above technical problem, in the first aspect, the embodiments of the present application provide a flow calculation method for a differential pressure type pulmonary function meter, and the method includes the following steps:

[0008] Obtain the pressure differences corresponding to different flows measured in real time by the pressure-taking device of the differential pressure type pulmonary function instrument during the calibration stage, and store the real-time measured pressure difference data and flow data into the pressure difference array and the flow array respectively to form a reference table; the different flows are generated by a flow generator with its outlet aligned with the inlet of the differential pressure type pulmonary function instrument.

[0009] Obtain the measured pressure difference data of the pressure-taking device of the differential pressure type pulmonary function instrument during the usage stage, and determine where the measured pressure difference data falls in the pressure difference array of the reference table.

[0010] If the measured pressure difference data is exactly the same as a certain reference pressure difference data in the pressure difference array of the reference table, then the reference flow data in the flow array corresponding to this reference pressure difference data is the flow corresponding to the measured pressure difference data.

[0011] If the measured pressure difference data falls between two reference pressure difference data in the pressure difference array of the reference table, use the interpolation method to calculate the flow corresponding to the measured pressure difference data.

[0012] Preferably, the flow generator generates different flows from small to large in sequence according to a set frequency.

[0013] More preferably, the interval between elements of the flow array is 0.03 - 0.07 L / S.

[0014] Preferably, the pressure difference corresponding to each flow in the flow array is stored in the corresponding serial number of the pressure difference array to form a reference table with a one-to-one correspondence between the flow and the pressure difference.

[0015] Preferably, the specific method for determining where the measured pressure difference data falls in the pressure difference array of the reference table is as follows:

[0016] Send the measured pressure difference data into a look-up table function, and query where the measured pressure difference data falls in the pressure difference array of the reference table through the look-up table function.

[0017] Furthermore, the specific steps for querying where the measured pressure difference data falls in the pressure difference array of the reference table through the look-up table function are as follows:

[0018] Divide the pressure difference array in the reference table into multiple different grade ranges according to certain rules;

[0019] Perform a loop judgment on the measured pressure difference data, compare the measured pressure difference data with each of the divided grade ranges in sequence, and determine the grade range where the measured pressure difference data is located;

[0020] Calculate the starting point of the search range according to the grade range where the measured pressure difference data is located, and then query the reference table to obtain the falling point of the measured pressure difference data in the pressure difference array of the reference table.

[0021] Preferably, the specific method for calculating the flow rate corresponding to the measured differential pressure data by the interpolation method is as follows:

[0022] Assume that the measured differential pressure data p falls between two reference differential pressure data p1 to p2 in the differential pressure array of the reference table, where p1 < p2, then:

[0023] f = f1 + (p - p1) * (f2 - f1) / (p2 - p1)

[0024] where f is the flow rate corresponding to the measured differential pressure data p, f1 is the flow rate corresponding to the reference differential pressure data p1, and f2 is the flow rate corresponding to the reference differential pressure data p2.

[0025] In a second aspect, an embodiment of the present application further provides a differential pressure type pulmonary function instrument flow rate calculation device, and the device includes:

[0026] A calibration module, configured to obtain the differential pressures corresponding to different flow rates measured in real time by the pressure taking device of the differential pressure type pulmonary function instrument during the calibration stage, and store the real-time measured differential pressure data and flow rate data into a differential pressure array and a flow rate array respectively to form a reference table; the different flow rates are generated by a flow generator with its outlet aligned with the inlet of the differential pressure type pulmonary function instrument;

[0027] A flow rate calculation module, configured to obtain the measured differential pressure data of the pressure taking device of the differential pressure type pulmonary function instrument during the use stage, and determine where the measured differential pressure data falls in the differential pressure array of the reference table;

[0028] If the measured differential pressure data is exactly the same as a certain reference differential pressure data in the differential pressure array of the reference table, then the reference flow rate data in the flow rate array corresponding to this reference differential pressure data is the flow rate corresponding to the measured differential pressure data;

[0029] If the measured differential pressure data falls between two reference differential pressure data in the differential pressure array of the reference table, then use the interpolation method to calculate the flow rate corresponding to the measured differential pressure data.

[0030] In a third aspect, an embodiment of the present application further provides a differential pressure type pulmonary function instrument flow rate calculation device, including a memory, a processor, and a computer program stored on the memory and executable on the processor, and when the processor executes the program, the steps of the above-mentioned differential pressure type pulmonary function instrument flow rate calculation method are implemented.

[0031] In a fourth aspect, an embodiment of the present application further provides a computer-readable storage medium, on which a computer program is stored, and characterized in that when the program is executed by a processor, the steps of the above-mentioned differential pressure type pulmonary function instrument flow rate calculation method are implemented.

[0032] One or more technical solutions provided in the embodiments of the present application have at least the following technical effects or advantages:

[0033] (1) High accuracy: Although traditional methods aim to improve accuracy through complex curve fitting, due to the computational complexity and excessive occupation of system resources, more errors may be introduced. For example, data loss or untimely processing caused by computational delay will make the final measurement result inaccurate.

[0034] While the method of the present invention can convert the pressure difference into flow more timely and accurately while ensuring relatively simple calculations, avoiding measurement errors caused by system delay and resource competition, improving the accuracy and consistency of measurement data, and providing more reliable data support for subsequent clinical diagnosis and treatment.

[0035] (2) Reduced computational complexity and improved real-time performance: When traditional methods process the sieve airway where the pressure difference and flow at both ends are non-linear, they need to fit complex curves through measured data, and in some cases, piecewise processing is also required, which will result in a very complex conversion formula obtained by fitting. When a complex formula is calculated in the MCU software, it will consume a large amount of system time and processor computing power, seriously affecting the real-time performance of the calculation result.

[0036] The method of the present invention is simple and convenient to calculate, avoids the use of complex formulas, reduces the requirement for the computing power of the MCU, improves the real-time performance of the calculation result, and helps to capture the instantaneous changes during the breathing process in real time.

[0037] (3) Improved system reliability and stability: Traditional complex calculations will occupy a large amount of MCU system resources, including the computing resources and memory resources of the processor, which may lead to a decline in system stability, such as jamming and crashing.

[0038] By optimizing the calculation method, the present invention reduces the occupation of system resources, enables the MCU to operate more stably during data acquisition and processing, reduces the risk of system failures caused by resource tension, and improves the reliability and stability of the system.

[0039] (4) Reduced cost: Since the present invention has a lower requirement for the computing power of the MCU, a relatively low-performance and low-cost MCU can be selected in hardware selection, reducing the hardware cost. At the same time, since the stability and real-time performance of the system are guaranteed, the method of the present invention has good applicability on different types and performance of MCUs, and there is no need to select high-end and expensive MCUs to meet complex calculation requirements, expanding the application scope of the pulmonary function instrument in different cost budgets and application scenarios, and having better cost performance.

[0040] In summary, the method of the present invention has significant advantages in terms of calculation accuracy, calculation efficiency, system real-time performance, system stability, and cost applicability, etc. It is suitable for being applied to an embedded system with high requirements for data acquisition real-time performance and system stability, and is particularly suitable for a differential pressure type pulmonary function instrument with a non-linear screen pressure-taking airway. BRIEF DESCRIPTION OF THE DRAWINGS

[0041] The accompanying drawings herein are incorporated into the specification and form a part of this specification, showing embodiments consistent with the present application, and are used together with the specification to explain the principles of the present application.

[0042] Figure 1 It is a flowchart of the flow calculation method for a differential pressure type pulmonary function instrument provided in Embodiment 1 of the present application;

[0043] Figure 2 It is a structural schematic diagram of the flow calculation device for a differential pressure type pulmonary function instrument provided in Embodiment 2 of the present application.

[0044] Through the above accompanying drawings, specific embodiments of the present application have been shown, and there will be more detailed descriptions hereinafter. These accompanying drawings and the textual descriptions are not intended to limit the scope of the concept of the present application in any way, but to illustrate the concept of the present application to those skilled in the art by referring to specific embodiments. DETAILED DESCRIPTION OF THE EMBODIMENTS

[0045] In order to better understand the above technical solutions, exemplary embodiments will be described in detail here, and the examples are shown in the accompanying drawings. When the following description refers to the accompanying drawings, unless otherwise indicated, the same numbers in different accompanying drawings represent the same or similar elements. The embodiments described in the following exemplary embodiments do not represent all embodiments consistent with the present application. On the contrary, they are merely examples of devices consistent with some aspects of the present application as detailed in the appended claims.

[0046] Embodiment 1

[0047] The differential pressure type pulmonary function instrument includes a pressure-taking device and a differential pressure sensor. When a patient breathes, the gas flows through the pipeline of the pulmonary function instrument, passes through the pressure-taking device, and different pressures are generated at different positions of the pressure-taking device. The differential pressure sensor measures the pressure difference before and after the pressure-taking device and calculates the flow rate of the patient's breathing based on the pressure difference.

[0048] This embodiment provides a flow calculation method for a differential pressure type pulmonary function instrument that is simple and accurate in calculation, Figure 1 It is a flowchart of the flow calculation method for a differential pressure type pulmonary function instrument provided in Embodiment 1 of the present application. The flow calculation method for the differential pressure type pulmonary function instrument includes the following steps:

[0049] Step S1: Calibration stage:

[0050] Align the outlet of the flow generator with the inlet of the differential pressure spirometer, so that the flow generator can generate different flow rates from small to large in sequence according to the set frequency;

[0051] The pressure differential corresponding to different flow rates is measured in real time through the pressure-taking device of the pressure differential spirometer, and the real-time measured pressure differential data and flow rate data are placed in the pressure differential array and flow rate array respectively, and stored in the device storage medium. The pressure differential corresponding to each flow rate in the flow array Flow is stored in the corresponding sequence number of the pressure differential array Pressure, forming a reference table with one-to-one correspondence between flow rate and pressure differential.

[0052] For the sake of clarity in the following description, the flow data in the flow array Flow of the reference table is referred to as reference flow data, and the pressure difference data in the pressure difference array Pressure of the reference table is referred to as reference pressure difference data.

[0053] In a preferred embodiment, the flow array Flow element interval is 0.03-0.07L / S, preferably 0.05L / S, which can ensure the accuracy of measurement. If the interval is too small, the fluctuation of the sensor itself will affect the pressure difference measurement; if the interval is too large, the subsequent linear interpolation deviation is large.

[0054] Step S2: Use phase:

[0055] When the user breathes toward the inlet of the pressure differential spirometer, the pressure differential is measured in real time by the pressure measuring device of the pressure differential spirometer, and it is determined where the measured pressure differential data falls in the pressure differential array of the reference table;

[0056] If the measured pressure difference data is exactly the same as a certain reference pressure difference data in the pressure difference array of the reference table, then the reference flow data in the flow array corresponding to the reference pressure difference data is the flow corresponding to the measured pressure difference data;

[0057] If the measured pressure difference data falls between two reference pressure difference data in the pressure difference array of the reference table, the flow corresponding to the measured pressure difference data is calculated using the interpolation method.

[0058] Further, the specific method for determining where the measured pressure difference data falls in the pressure difference array of the reference table is:

[0059] The measured pressure difference data is sent to a table lookup function, and the table lookup function is used to query where the measured pressure difference data falls in the pressure difference array of the reference table.

[0060] The specific steps are as follows:

[0061] S21, dividing the pressure difference array in the reference table into a plurality of different level ranges according to certain rules;

[0062] Specifically, these level ranges can be determined according to actual application requirements and the distribution characteristics of differential pressure data. For example, the differential pressure can be divided into several continuous intervals according to its magnitude, and each interval represents a level range. When dividing the level ranges, it is necessary to ensure that adjacent level ranges neither overlap nor cover the entire possible value range of the differential pressure data, so as to ensure the accuracy and integrity of subsequent searches.

[0063] Exemplarily, the differential pressure array in the reference table is divided into a pre-lookup table array containing 15 elements, and the elements are the differential pressures corresponding to the flow rate ranges from 0 to 14 L / S at intervals of 1 L / S.

[0064] S22. Perform a loop judgment on the measured differential pressure data, compare the measured differential pressure data with each of the divided level ranges in turn, and determine the level range where the measured differential pressure data is located.

[0065] Specifically, a loop statement (such as a for or while loop, depending on the programming language) can be used to traverse each level range. During the loop, check whether the measured differential pressure data meets the boundary conditions of the level range to determine the level range where it is located.

[0066] S23. Calculate the starting point of the search range based on the level range where the measured differential pressure data is located, and then query the reference table to obtain the falling point of the measured differential pressure data in the differential pressure array of the reference table.

[0067] Specifically, once the level range where the measured differential pressure data is located is determined, calculate the starting point of the search range based on the information of this level range. This starting point will be used as the basis for finding the falling point of the measured differential pressure data in the reference table. The specific method for calculating the starting point may vary depending on the division method of the level range. For example, if the level range is equally spaced, the starting point can be calculated based on the boundaries and spacing of the level range; if it is non-equally spaced, predefined mapping relationships or other calculation rules may be required to determine the starting point.

[0068] Based on the calculated starting point, perform further search operations in the reference table to finally determine the falling point of the measured differential pressure data in the differential pressure array of the reference table. The search process may involve an ordered traversal of the reference table or other search algorithms (such as binary search, etc.), depending on the structure and storage method of the reference table. Select a more optimal search method according to the data length of each level range to achieve the purpose of fast calculation.

[0069] Exemplarily:

[0070] The binary search method is an algorithm for finding a specific element in an ordered array. Each comparison divides the array into two parts. By comparing the size relationship between the middle element and the target value, it is determined whether to continue searching in the left half or the right half. After each comparison, the search range is halved.

[0071] Assume that the initial length of the array is n. Each time a comparison is made, the search interval is reduced to half of the original. After log2n comparisons, the search range will be reduced to 1, that is, the target value is found or it is determined that the target value does not exist. Therefore, the time complexity of the binary search method is O(logn).

[0072] The traversal method refers to performing an access operation on each element in a data structure. For example, traversing an array from start to end and checking whether each element is the target element in turn.

[0073] Assume that there are n elements in the array. In the worst case, it is necessary to access n times to find the target element (if the target element is in the last position or does not exist in the array), or to complete the operation on all elements (such as calculating the sum of array elements, etc.). The execution time of the algorithm is proportional to the scale n of the input data, so the time complexity is O(n).

[0074] In summary, the time complexity of the binary search method is O(logn), and the time complexity of the traversal method is O(n). The binary search method is more efficient, and the binary search method is preferred.

[0075] During the search process, based on the starting point information and the magnitude of the measured pressure difference data, find the two adjacent pressure difference data closest to the measured pressure difference data. The position determined by these two adjacent pressure difference data is the falling point of the measured pressure difference data in the pressure difference array.

[0076] Furthermore, the specific method for calculating the flow rate corresponding to the measured pressure difference data by the interpolation method is as follows:

[0077] Suppose the measured pressure difference data p falls between two reference pressure difference data p1~p2 in the pressure difference array of the reference table, and p1 < p2, then there is:

[0078] f = f1 + (p - p1) * (f2 - f1) / (p2 - p1)

[0079] Among them, f is the flow rate corresponding to the measured pressure difference data p, f1 is the flow rate corresponding to the reference pressure difference data p1, and f2 is the flow rate corresponding to the reference pressure difference data p2.

[0080] Next, a specific application example is used to make a comparative explanation by using the method of this embodiment and the traditional formula fitting method respectively.

[0081] Calibration stage:

[0082] Align the outlet of the flow generator with the inlet of the differential pressure spirometer, so that the flow generator generates an airflow from 0.05 to 14 L / S, in steps of 0.05 L / S. The pressure differential corresponding to different flow rates is measured, recorded and stored in real time by the pressure taking device of the differential pressure spirometer, forming a reference table with one-to-one correspondence between flow rates and pressure differentials. For specific data, see Table 1. For the convenience of display, Table 1 only lists data in the range of 1 to 14 L / S and intervals of 1 L / S.

[0083] The traditional formula fitting method is used to fit the relationship formula between pressure difference and flow rate.

[0084] Use phase:

[0085] When the patient breathes toward the inlet of the pressure differential spirometer, the pressure difference is measured in real time through the pressure taking device of the pressure differential spirometer;

[0086] Traditional formula fitting method: Substitute the measured pressure difference data into the pressure difference and flow rate relationship formula fitted by the traditional formula fitting method to obtain the flow rate corresponding to the measured pressure difference data. The specific data is shown in Table 1.

[0087] Table 1 Comparison of flow data obtained using the traditional fitting formula and the table lookup method of this embodiment

[0088]

[0089] The table lookup method of this embodiment: determine where the measured pressure difference data falls in the pressure difference array of the reference table; if the measured pressure difference data is exactly the same as a certain reference pressure difference data in the pressure difference array of the reference table, then the reference flow data in the flow array corresponding to the reference pressure difference data is the flow corresponding to the measured pressure difference data; if the measured pressure difference data falls between two reference pressure difference data in the pressure difference array of the reference table, then the flow corresponding to the measured pressure difference data is calculated by interpolation method, and the specific data is shown in Table 1.

[0090] It can be seen from Table 1 that, compared with the flow rate calculated by the traditional formula fitting method, the flow rate obtained by the table lookup and interpolation calculation method provided by this embodiment has a smaller deviation in both low flow area and high flow area, indicating that the method provided by this embodiment has better accuracy than the traditional formula fitting method.

[0091] In addition, it is worth noting that since the method of this embodiment does not involve a specific pressure differential airway form, the nonlinear mesh airway described above is only a carrier form, and therefore the method of this embodiment can also be applied to pressure differential spirometers including but not limited to the following types of airways: linear mesh airways, throttling type, orifice plate type, Pitot tube type, Venturi tube, and other airways that can form a pressure difference.

[0092] The differential pressure type pulmonary function instrument flow calculation method provided in the above embodiment is applicable to both inhalation and exhalation detection.

[0093] Embodiment 2

[0094] Based on the same inventive concept as the differential pressure type pulmonary function instrument flow calculation method in the foregoing Embodiment 1, this embodiment also provides a differential pressure type pulmonary function instrument flow calculation device, as Figure 2 shown, the device includes:

[0095] A calibration module 10, configured to obtain the differential pressures corresponding to different flows measured in real time by the pressure taking device of the differential pressure type pulmonary function instrument during the calibration stage, and store the real-time measured differential pressure data and flow data into a differential pressure array and a flow array respectively to form a reference table; the different flows are generated by a flow generator with its outlet aligned with the inlet of the differential pressure type pulmonary function instrument;

[0096] A flow calculation module 20, configured to obtain the measured differential pressure data of the pressure taking device of the differential pressure type pulmonary function instrument during the use stage, and determine where the measured differential pressure data falls in the differential pressure array of the reference table;

[0097] If the measured differential pressure data is exactly the same as a certain reference differential pressure data in the differential pressure array of the reference table, then the reference flow data in the flow array corresponding to the reference differential pressure data is the flow corresponding to the measured differential pressure data;

[0098] If the measured differential pressure data falls between two reference differential pressure data in the differential pressure array of the reference table, the flow corresponding to the measured differential pressure data is calculated by interpolation.

[0099] The various specific processes and specific examples of the differential pressure type pulmonary function instrument flow calculation method in the foregoing Embodiment 1 are equally applicable to the differential pressure type pulmonary function instrument flow calculation device in this embodiment. Through the detailed description of Embodiment 1, those skilled in the art can clearly know the implementation method of the differential pressure type pulmonary function instrument flow calculation device in this embodiment. Therefore, for the sake of simplicity of the specification, it will not be elaborated here.

[0100] Embodiment 3

[0101] Based on the same inventive concept as the differential pressure type pulmonary function instrument flow calculation method in the foregoing Embodiment 1, this embodiment also provides a differential pressure type pulmonary function instrument flow calculation device, on which a computer program is stored, and when the program is executed by a processor, it implements the steps of the differential pressure type pulmonary function instrument flow calculation method described in Embodiment 1.

[0102] Embodiment 4

[0103] Based on the same inventive concept as the differential pressure type pulmonary function instrument flow calculation method in the foregoing Embodiment 1, this embodiment also provides a computer-readable storage medium, on which a computer program is stored, and when the program is executed by a processor, the steps of the differential pressure type pulmonary function instrument flow calculation method described in Embodiment 1 are implemented.

[0104] Those skilled in the art should understand that the embodiments of the present application can be provided as methods, systems, or computer program products. Therefore, the present application can take the form of a complete hardware embodiment, a complete software embodiment, or an embodiment combining software and hardware aspects. Moreover, the present application can take the form of a computer program product implemented on one or more computer-usable storage media (including but not limited to disk storage, CD-ROM, optical storage, etc.) containing computer-usable program code.

[0105] The present application is described with reference to the flowcharts and / or block diagrams of methods, devices (systems), and computer program products according to the embodiments of the present application. It should be understood that each flow and / or block in the flowchart and / or block diagram can be implemented by computer program instructions, and the combination of the flows and / or blocks in the flowchart and / or block diagram can also be implemented by computer program instructions. These computer program instructions can be provided to the processor of a general-purpose computer, a special-purpose computer, an embedded processor, or other programmable data processing devices to generate a machine, so that the instructions executed by the processor of the computer or other programmable data processing devices generate a device for implementing the functions specified in one Figure 1 one flow or multiple flows and / or blocks Figure 1 one block or multiple blocks.

[0106] These computer program instructions can also be stored in a computer-readable memory that can direct a computer or other programmable data processing device to work in a specific manner, so that the instructions stored in the computer-readable memory generate a manufactured article including an instruction device, and the instruction device implements the functions specified in one Figure 1 one flow or multiple flows and / or blocks Figure 1 one block or multiple blocks.

[0107] These computer program instructions can also be loaded onto a computer or other programmable data processing device, so that a series of operation steps are executed on the computer or other programmable device to generate a computer-implemented process, and thus the instructions executed on the computer or other programmable device provide steps for implementing the functions specified in one Figure 1 one flow or multiple flows and / or blocks Figure 1 one block or multiple blocks.

[0108] Although the preferred embodiments of the present application have been described, additional changes and modifications can be made to these embodiments by those skilled in the art once they learn the basic creative concept. Therefore, the appended claims are intended to be construed to include the preferred embodiments as well as all changes and modifications falling within the scope of the present application.

[0109] Obviously, those skilled in the art can make various changes and modifications to the present application without departing from the spirit and scope of the present application. Thus, if these modifications and variations of the present application fall within the scope of the claims of the present application and their equivalent technologies, the present application is also intended to include these modifications and variations.

Claims

1. A method for calculating flow rate of a pressure differential pulmonary function instrument, characterized in that: The method includes the following steps: Obtain the pressure differences corresponding to different flows measured in real time by the pressure-taking device of the differential pressure type pulmonary function instrument during the calibration stage, and store the real-time measured pressure difference data and flow data into a pressure difference array and a flow array respectively to form a reference table; the different flows are generated by a flow generator with its outlet aligned with the inlet of the differential pressure type pulmonary function instrument; Obtain the measured pressure difference data of the pressure-taking device of the differential pressure type pulmonary function instrument during the usage stage, and determine where the measured pressure difference data falls in the pressure difference array of the reference table; If the measured pressure difference data is exactly the same as a certain reference pressure difference data in the pressure difference array of the reference table, the reference flow data in the flow array corresponding to this reference pressure difference data is the flow corresponding to the measured pressure difference data; If the measured pressure difference data falls between two reference pressure difference data in the pressure difference array of the reference table, calculate the flow corresponding to the measured pressure difference data using the interpolation method.

2. The flow calculation method of the pressure differential pulmonary function instrument according to claim 1, characterized in that: Make the flow generator generate different flows from small to large in sequence according to the set frequency.

3. The flow calculation method of the pressure differential pulmonary function instrument as claimed in claim 2, characterized in that: The interval of the elements in the flow array is 0.03 - 0.07 L / S.

4. The flow calculation method of the pressure differential pulmonary function instrument as claimed in claim 1, characterized in that: The pressure difference corresponding to each flow in the flow array is stored in the corresponding serial number in the pressure difference array, forming a reference table with one-to-one correspondence between flow and pressure difference.

5. The flow calculation method of the pressure differential pulmonary function instrument as claimed in claim 1, characterized in that: The specific method for determining where the measured pressure difference data falls in the pressure difference array of the reference table is: Send the measured pressure difference data into a look-up table function, and query where the measured pressure difference data falls in the pressure difference array of the reference table through the look-up table function.

6. The flow calculation method of the pressure differential pulmonary function instrument as claimed in claim 5, characterized in that: The specific steps for querying where the measured pressure difference data falls in the pressure difference array of the reference table through the look-up table function are as follows: Divide the pressure difference array in the reference table into multiple different grade ranges according to certain rules; Perform a loop judgment on the measured pressure difference data, compare the measured pressure difference data with each of the divided grade ranges in sequence, and determine the grade range where the measured pressure difference data is located; Calculate the starting point of the search range according to the grade range where the measured pressure difference data is located, and then query the reference table to obtain the falling point of the measured pressure difference data in the pressure difference array of the reference table.

7. The flow calculation method of the pressure differential pulmonary function instrument as claimed in claim 1, characterized in that: The specific method for calculating the flow corresponding to the measured pressure difference data using the interpolation method is: Assume that the measured pressure difference data p falls between two reference pressure difference data p1 - p2 in the pressure difference array of the reference table, and p1 < p2, then there is: f = f1 + (p - p1) * (f2 - f1) / (p2 - p1) where f is the flow corresponding to the measured pressure difference data p, f1 is the flow corresponding to the reference pressure difference data p1, and f2 is the flow corresponding to the reference pressure difference data p2.

8. A flow calculation device for a pressure differential pulmonary function instrument, characterized in that: The device includes: A calibration module, which is used to obtain the pressure differences corresponding to different flows measured in real time by the pressure-taking device of the differential pressure type pulmonary function instrument during the calibration stage, and store the real-time measured pressure difference data and flow data into a pressure difference array and a flow array respectively to form a reference table; the different flows are generated by a flow generator with its outlet aligned with the inlet of the differential pressure type pulmonary function instrument; A flow calculation module, which is used to obtain the measured pressure difference data of the pressure-taking device of the differential pressure type pulmonary function instrument during the usage stage, and determine where the measured pressure difference data falls in the pressure difference array of the reference table; If the measured pressure difference data is exactly the same as a certain reference pressure difference data in the pressure difference array of the reference table, then the reference flow data in the flow array corresponding to the reference pressure difference data is the flow corresponding to the measured pressure difference data; If the measured pressure difference data falls between two reference pressure difference data in the pressure difference array of the reference table, the flow rate corresponding to the measured pressure difference data is calculated using the interpolation method.

9. A flow calculation device for a pressure differential pulmonary function instrument, comprising a memory, a processor, and a computer program stored in the memory and executable on the processor, characterized in that: When the processor executes the program, the steps of the flow calculation method of the pressure difference spirometer as described in any one of claims 1 to 7 are implemented.

10. A computer-readable storage medium having a computer program stored thereon, characterized in that: When the program is executed by a processor, the steps of the flow calculation method of the pressure difference spirometer as claimed in any one of claims 1 to 7 are implemented.

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